IMPLANTABLE DEVICE FOR DETERMINING A FLUID VOLUME FLOW THROUGH A BLOOD VESSEL

Abstract

The invention relates to an implantable device (1) for determining a fluid volume flow (2) through a blood vessel (3), comprising: —at least one sensor (4) for recording at least one flow parameter, —a retaining means (5) for retaining a vessel wall port (6) in the region of a vessel wall (7) of the blood vessel (3), wherein the retaining means (5) is formed to retain the at least one sensor (4) in the region of the vessel wall (7).

Description

The invention relates to an implantable device for determining a fluid volume flow through a blood vessel, an arrangement, a method for determining a fluid volume flow through a blood vessel in the region of an implanted device, and the use of a device. The invention is used in particular for (fully) implanted left heart assist systems (LVAD [Left Ventricular Assist Device]).

Implanted left heart assist systems (LVAD) exist mainly in two variants. On the one hand, there are (percutaneous) minimally-invasive left heart assist systems. The second variant are left heart assist systems invasively implanted under the rib cage. The first variant circulates blood directly from the left ventricle into the aorta, because the (percutaneous) minimally invasive left heart assist system is positioned in the center of the aortic valve. The second variant circulates the blood from the apical region from the left ventricle via a bypass tube into the aorta.

The task of a cardiac assist system is to circulate blood. The so-called heart-time-volume (HTV, usually stated in liters per minute) has high clinical relevance in this case. In other words, the heart-time volume affects the total volume flow of blood from a ventricle, particularly from the left ventricle to the aorta. Accordingly, the initial task is to determine this parameter as a metrology value while a cardiac assist system is in operation.

Depending on the level of assistance, which describes the share of the volume flow from the ventricle to the aorta conveyed by a circulation means, such as a pump of the assist system, a certain volume flow reaches the aorta via the physiological path through the aortic valve. The heart-time volume or the total volume flow (Q_HTV) from the ventricle to the aorta is therefore usually the sum of the pump volume flow (Q_p) and the aortic valve volume flow (Q_a).

An established method for determining the heart-time volume (Q_HTV) in the clinical setting is the use of dilution methods, all of which, however, rely on a catheter inserted transcutaneously and therefore can only provide heart-time volume measurement data during cardiac surgery or directly thereafter during the subsequent stay in intensive care. An established method for measuring the pump volume flow (Q_p) is the correlation of the operating parameters of the assist system, predominantly the electrical power consumption, possibly supplemented by further physiological parameters, such as the blood pressure. The integration of dedicated ultrasound measurement technology into an assist system has also already been proposed. It should be noted here that the mentioned ultrasonic metrology only measures the pump volume flow and cannot record a bypass flow through the aortic valves past the assist system.

A (fully) implanted recording of the heart-time volume, i.e. of Q_HTV, in particular by the assist system itself, is not disclosed in the prior art. Fully implanted in this case in particular means that the means required for recording are completely in the patient's body and remain there. This makes it possible to record the heart-time volume even outside of heart surgery.

Proceeding from the foregoing, the invention is based on the task of specifying an implantable device or a method for improved flow detection in a blood vessel.

According to Claim 1, an implantable device is proposed herein for determining a fluid volume flow through a blood vessel, comprising:

• • at least one sensor for detecting at least one flow parameter,
  • a retaining means for retaining a vessel wall port in the region of a vessel wall of the blood vessel,

wherein the retaining means is further formed to retain the at least one sensor in the region of the vessel wall.

The device can be implanted. Furthermore, the assist system is preferably fully implantable. In other words, this means in particular that the means required for recording, in particular the at least one ultrasonic sensor, are (completely) located in the body of the patient and remain there. In addition, the retaining means and the vessel wall port are also (completely) located and principally also remain in the patient's body. However, it is not mandatory for a supply cable and/or a control unit or the analysis unit of the device to be (completely) arranged in the patient's body. For example, the device can be implanted such that the analysis unit of the device is arranged on the skin of the patient or outside the body of the patient and a connection is established to the sensor arranged in the body. In other words, this connection, for example in the form of a supply cable, can lead out of the body.

The fluid volume flow through the blood vessel in particular indicates how much volume of the fluid per unit of time is transported or flows through a (specific and/or flow-carrying) blood vessel cross-section. In particular, the device is configured for determining a fluid volume flow through a blood vessel cross-section in the region of the device. The fluid volume flow is preferably a total fluid volume flow or the so-called heart-time volume (formula symbol: Q_HTV), which describes the total fluid volume from a ventricle. This total fluid volume flow (Q_HTV) is usually the sum of the so-called pump volume flow (Q_p) and the so-called aortic valve volume flow (Q_A). The pump volume flow (Q_p) generally quantifies the flow that flows (only) through the assist system itself, for example through a (inlet) cannula of the assist system. The aortic valve volume flow (Q_A) regularly quantifies the flow that flows past the assist system through the aortic valve.

The blood vessel is preferably an artery. The blood vessel can for example be the aorta, in particular the part of the aorta ascending to the aortic arch, or the pulmonary trunk (Truncus pulmonalis) in the two pulmonary arteries. If the device is used in connection with a left heart assist system, the blood vessel is preferably the aorta. If the device is used in connection with a right heart assist system, the blood vessel is preferably the pulmonary trunk (Truncus pulmonalis) in the two pulmonary arteries.

The device comprises at least one sensor for recording at least one flow parameter. The sensor can, for example, have at least one ultrasonic transducer, at least one radar antenna, and/or at least one laser source. In other words, this means, in particular, that the sensor can for example be formed in the manner of an ultrasonic sensor, a radar sensor and/or a laser Doppler sensor (laser Doppler velocimeter). The at least one flow parameter is preferably a flow velocity and/or a fluid volume flow, in particular a total fluid volume flow. If a flow velocity is recorded by means of the sensor, the flow velocity recorded for determining the fluid volume flow can for example be multiplied by a (flow carrying) blood vessel cross-section (in the region of the device).

In addition, the device comprises a retaining means for retaining a vessel wall port in the region of a vessel wall of the blood vessel. The vessel wall port is usually set up to form an artificial passage through the vessel wall of the blood vessel or to keep an artificial opening in the vessel wall open. In other words, this means in particular that the vessel wall port can be used to form an artificial passage through a vessel wall of a blood vessel or to keep open an artificial opening in the vessel wall. For example, the vessel wall port can be formed in the manner of a ring, which is inserted into or penetrates the vessel wall and is formed from a material that can be used for medical purposes. The retaining means is in particular formed to retain or secure the vessel wall port in its intended position (in relation to the vessel wall). Preferably, the retaining means is formed to retain the vessel wall port at a (specific) position along a blood vessel circumference and/or the flow direction in the vessel wall, preferably the (ascending) aorta or the pulmonary trunk (Truncus pulmonalis) in the two pulmonary arteries.

In addition, the retaining means is formed to retain the at least one sensor in the region of the vessel wall, in particular the aorta or the pulmonary trunk, in the two pulmonary arteries. By an arrangement in or on the aorta or in or on the pulmonary trunk in the two pulmonary arteries, it can be achieved in a particularly advantageous manner that the entire fluid volume flow (total fluid volume flow) from the respective (left or right) ventricle can be recorded by means of the sensor.

The device is advantageously formed for carrying out a method proposed here.

In other words, in particular also an implantable device for determining a fluid volume flow through a blood vessel can be proposed here, comprising:

• • a vessel wall port with which an artificial passage can be formed through a vessel wall of a blood vessel,
  • a retaining means for retaining a vessel wall port in the region of a vessel wall of the blood vessel,
  • at least one sensor for recording at least one flow parameter, which is retained on the retaining means.

According to an advantageous embodiment, it is proposed that the sensor comprises an ultrasonic element. The ultrasonic element is preferably an ultrasonic transducer element. In particular, precisely or only one ultrasonic sensor is provided. The ultrasonic sensor preferably comprises precisely or only one ultrasonic transducer element. This is sufficient particularly if a pulsed Doppler measurement is to be performed or if the PWD method is to be used.

According to an advantageous embodiment, it is proposed that the sensor be formed to carry out a pulsed Doppler method. In other words, this means in particular that the sensor is formed to carry out a so-called Pulsed Wave Doppler (PWD) method. A PWD measurement cycle comprises in particular a sequence of a (defined) number of successively emitted ultrasonic pulses. A new ultrasonic pulse is usually sent out only if all (significant) echoes of an ultrasonic pulse sent out immediately beforehand have dissipated and/or were received.

According to an advantageous embodiment, it is proposed that the sensor be formed for recording a blood vessel flow-carrying cross-section. In other words, this means in particular that the sensor is formed to measure a flow-carrying blood vessel cross-section in the region of the device. In connection with an ultrasonic measurement, an analysis of the time of flight between the emitted pulse and the received vessel wall echo can for example be carried out. The spatial dimensions (within the blood vessel) can be inferred from this, in particular at a known speed of sound in the propagation medium. It can be specified that the flow-carrying blood vessel cross-section be recorded repeatedly. Alternatively, the flow-carrying blood vessel cross-section (which in the chronological mean generally exhibits no significant change versus time) can be recorded once and stored in a memory, for example of a control unit or an analysis unit.

According to an advantageous embodiment, it is proposed that the at least one sensor comprises two ultrasonic elements. The two ultrasonic elements are preferably positioned at an offset to one another in the direction of flow. In other words, this means in particular that one ultrasonic element is arranged upstream of the other ultrasonic element. Furthermore, the two ultrasonic elements are preferably arranged opposite each other and aligned facing each other. This allows a measurement to be carried out between the two ultrasonic elements in an advantageous manner, wherein the direction of propagation of the ultrasonic signals together with the (main) flow direction describes an angle of less than or greater than 90° (but not exactly 90°). The two ultrasonic elements are particularly preferably arranged opposite each other and aligned facing each other such that the connecting line between the two ultrasonic elements extends centrally through a cross-section of the flow-carrying blood vessel.

Instead of placing the ultrasonic elements opposite each other, the ultrasonic elements can also be positioned next to each other on one side of the blood vessel. In this case, a reflector is preferably specified on the opposite side of the blood vessel, which can reflect the sound pulses to the respectively receiving ultrasonic element.

Furthermore, it can be specified that the at least one sensor comprises more than two ultrasonic elements. The best-suited pairs of ultrasonic element elements can, for example, be identified with time of flight measurements, and the measurement can then be carried out with these.

According to an advantageous embodiment, it is proposed that the sensor can change a main beam direction the sensor. The sensor is preferably formed for carrying out beam steering.

According to an advantageous embodiment, it is proposed that the retaining means be formed in the form of a cuff that at least partially circumferentially enwraps the blood vessel. The cuff preferably circumferentially enwraps the blood vessel or a circumference of the blood vessel to at least 80% or even completely. Furthermore, the retaining means is preferably formed from a material suitable for medical purposes, for example using silicone.

According to an advantageous embodiment, it is proposed that the retaining means be formed to retain the at least one sensor in or on the vessel wall. For this purpose, the retaining means can form a pocket in which the sensor is accommodated. The retaining means is preferably formed to retain the at least one sensor on an outer side or an outer circumference of the vessel wall. The retaining means is particularly preferably formed to retain two ultrasonic elements such that they are arranged opposite one another and are aligned facing one another, so that the connecting line between the two ultrasonic elements extends centrally through a cross-section of the flow-carrying blood vessel.

According to an advantageous embodiment, it is proposed that the vessel wall port have a feed through for a (electrical) cable or an opening for a bypass line. For this purpose, the vessel wall port can be formed in the shape of a ring, which is inserted into or can penetrate the vessel wall and is in particular formed from a material that can be used for medical purposes. The bypass line is generally specified and formed to connect a left ventricle or an assist system connected to the left ventricle with an aorta by bypassing the aortic valve.

According to another aspect, an arrangement is proposed, comprising a device according to any of the above claims and an implantable vascular assist system. The arrangement can further comprise at least one supply cable, a control unit, and/or an analysis unit. The analysis unit can for example be connected to the sensor of the device (by signal technology). The control unit can, for example, be connected to the assist system and/or the analysis unit (by signal technology). In addition, it can be specified that the analysis unit is (additionally) integrated in the control unit.

The vascular assist system is preferably a cardiac assist system, particularly preferably a ventricular assist system. The assist system is regularly used to assist the conveyance of blood in the cardiovascular system of humans, or patients if applicable. The assist system can be arranged at least partially in a blood vessel. The blood vessel is, for example, the aorta, particularly in the case of a left heart assist system, or the pulmonary trunk (Truncus pulmonalis) into the two pulmonary arteries, particularly in the case of a right heart assist system. The support system is preferably arrangeable at the outlet of the left ventricle of the heart or the left ventricle. The assist system is particularly preferably arrangeable in the aortic valve position.

The assist system is preferably a left-ventricular heart assist system (LVAD) or a percutaneous, minimally invasive left heart assist system. Furthermore, it is preferred that the assist system can be fully implanted. In other words, this means in particular that the means required for conveying blood, in particular a flow machine of the assist system, are completely located in the body of the patient and remain there. However, it is not mandatory that a control unit or an analysis unit of the assist system is also arranged in the body of the patient. For example, the assist system can be implanted such that the control unit or the analysis unit is arranged on the skin of the patient or outside the body of the patient and a connection is established to the flow machine arranged in the body. The assist system is particularly preferably configured and/or suitable for being arranged at least partially in a ventricle, preferably in the left ventricle of a heart, and/or in an aorta, in particular in the aortic valve position.

The assist system furthermore preferably comprises a cannula, in particular an inlet cannula, a flow machine, such as a pump and/or an electric motor. The electric motor is in this case regularly a component of the flow machine. The (inlet) cannula is preferably configured such that in the implanted state, it can guide fluid from a (left) ventricle of a heart to the flow machine. The assist system is preferably elongated and/or tubular. The cannula and the flow machine are preferably arranged in the region of opposite ends of the assist system.

According to an advantageous embodiment, it is proposed that the vessel wall port of the device have a feed through for a (electrical) cable of the assist system or an opening for a bypass line of the assist system. A feed through for a cable of the assist system is provided in particular if the assist system is an (left heart) assist system implantable in aortic valve position. An opening for a bypass line of the assist system is specified in particular if the assist system is an apically implantable (left heart) assist system.

According to another aspect, a method for determining a fluid volume flow through a blood vessel in the region of an implanted device is proposed, comprising the following steps:

• a) perform a measurement with at least one sensor of the device, which is retained with a retaining means for retaining a vessel wall port in the region of a vessel wall of the blood vessel,
• b) provide a measurement result from step a),
• c) determine the fluid volume flow using the measurement result provided in step b).

The method is preferably carried out with a device presented here and/or an arrangement presented here. A pulsed Doppler measurement is preferably carried out in step a). Furthermore, it is preferred that in step c) a flow velocity measured by means of the sensor is multiplied by a known or measured (by means of the sensor) blood vessel cross-section. Alternatively, a (calibration) data set stored in the sensor and/or in a control or analysis unit can for example be used in step c), the data set providing a direct relationship between the measurement result and the fluid volume flow.

According to another aspect, use of a device proposed here for determining a fluid volume flow through a blood vessel is proposed.

The details, features, and advantageous embodiments discussed in connection with the device can also occur accordingly in the arrangement, the method and/or the use presented here and vice versa. In this respect, reference is made in full to the discussion therein regarding the detailed characterization of the features.

The solution presented here as well as its technical environment are explained in more detail below with reference to the figures. It is important to note that the invention is not limited by the shown exemplary embodiments. In particular, unless explicitly stated otherwise, it is also possible to extract partial aspects of the facts explained in the figures and to combine them with other components and/or insights from other figures and/or the present description. The following are shown schematically:

FIG. 1 an arrangement proposed herein,

FIG. 2 a further arrangement proposed herein,

FIG. 3 a device proposed herein,

FIG. 4 a further device proposed herein in a cross-sectional view,

FIG. 5 the device according to FIG. 3 in a further cross-sectional view, and

FIG. 6 a sequence of a method presented herein in a standard operating procedure,

FIG. 1 shows schematically an arrangement 14 proposed herein. The arrangement 14 comprises a device 1 proposed herein and an implantable vascular (here: ventricular) assist system 15. The arrangement is shown herein in an exemplary implanted state, wherein the assist system 15 passes through an aortic valve 17 and protrudes into a left ventricle 16. This illustrates an exemplary embodiment of an implanted left ventricular heart assist system 15 in the aortic valve position. In addition, the device 1 is arranged in the region of an ascending aorta 3.

The device 1 shown herein in an exemplary implanted state is formed to determine a fluid volume flow 2 through a blood vessel 3 (here the aorta). For this purpose, the device 1 comprises a sensor 4 for recording at least one flow parameter (here: the fluid volume flow 2) and a retaining means 5 for retaining a vessel wall port 6 in the region of a vessel wall 7 of the blood vessel 3. Here, the retaining means 5 is formed to retain the at least one sensor 4 in the region of the vessel wall 7.

The vessel wall port 6 of the device 1 in this case comprises a feed through 10 for a cable 11 of the assist system 15. The vessel wall port 6 or the feed through 10 in this case serves as an example for feeding out an electrical supply cable 11 for a (fully) implanted assist system 15 in the aortic valve position. In other words, the vessel wall port 6 forms in particular a port component of the device 1.

FIG. 2 shows schematically another arrangement 14 proposed herein. The arrangement 14 comprises a device 1 proposed herein, an implantable vascular (here: ventricular) assist system 15, and a control unit 20. The reference symbols are used uniformly so that reference can be made to the above explanations.

FIG. 2 illustrates an exemplary embodiment of an apically implanted left ventricular heart assist system 15. According to the illustration according to FIG. 2, the vessel wall port 6 of the device 1 has an opening 12 for a bypass line 13 of the assist system 15. The vessel wall port 6 or the opening 12 in this case serve as an example for recirculating a pump volume conveyed into the cardiovascular system by means of the assist system 1.

The control unit 20 can also be implanted (for fully implanted systems). However, this is not mandatory. In transcutaneous systems, for example, a first supply line 18 and a second supply line 19 can be guided through the skin to an extracorporeal control unit 20.

FIG. 3 shows schematically a device 1 proposed herein. The reference symbols are used uniformly so that reference can be made to the above explanations.

The retaining means 5 is in this case formed by way of example to retain the sensor 4 on the vessel wall 7. Furthermore, the retaining means 5 is formed by way of example in the shape of a cuff that at least partially circumferentially enwraps the blood vessel 3. The design as a cuff allows in an advantageous manner for a higher mechanical stability to be achieved and for the presence of installation space for sensors, for example ultrasonic transducers.

In FIG. 3, the sensor 4 comprises an ultrasonic element 8. In addition, the sensor 4 is formed for carrying out a pulsed Doppler method.

The flow calculation can be carried out using a single ultrasonic transducer 8 according to the Pulsed Wave Doppler method (PWD method). The ultrasonic transducer 8 sends an ultrasonic pulse and analyzes the phase progression of the sound energy back scattered on the cellular components of the blood in the time measurement window. In addition, large acoustic impedance differences, such as those occurring between blood and the aortic wall, can be detected in the transient reception signal.

Furthermore, the sensor 4 is shown here by way of example for recording a flow-carrying blood vessel cross-section 9 (not shown here, cf. FIG. 4).

The spatial dimensions can be inferred from an analysis of the time of flight between the emitted pulse and the received aortic wall echo at a known speed of sound in the propagation medium. By combining both methods, it is possible to calculate the flow velocity with the Doppler method and to calculate the cross-sectional area of the aorta with the echo time of flight, so that the volume flow can be recorded or calculated with the best possible precision.

FIG. 4 shows schematically a further device 1 proposed herein in a cross-sectional view. The reference symbols are used uniformly so that reference can be made to the above explanations.

In FIG. 4, the one sensor 4 comprises two ultrasonic elements 8. The two ultrasonic elements 8 are positioned at an offset to one another in flow direction. Furthermore, the two ultrasonic elements 8 are arranged opposite each other and aligned facing each other. The illustration according to FIG. 4 illustrates by way of example the position of the ultrasonic transducers or ultrasonic elements 8 to each other.

FIG. 4 shows an exemplary embodiment wherein two ultrasonic transducers 8 are placed opposite the cuff 5. A pulsed ultrasonic method can also be used here. If the transducers 8 are not positioned orthogonally to the flow direction of the blood, the flow rate can be inferred based on the time of flight differences of the pulses from one ultrasonic element 8 to the other ultrasonic element 8 independently of the speed of sound in the medium. By means of the mean value of the signal time of flight, the geometry and thus the aortic cross-section 9 can also be inferred. It is advantageous for the method when low-focus ultrasonic transducers (ultrasonic elements) are used so that the method can remain operational even for poor positions of the sensors or the ultrasonic elements to each other (e.g. due to poor positioning or due to movement in the region of the aorta).

FIG. 5 schematically shows the device according to FIG. 4 in a further cross-sectional view.

Here, it is shown by way of example that the two ultrasonic elements 8 are arranged opposite each other and aligned facing each other such that the connecting line between both elements 8 extends centrally through the cross-section of the blood vessel to be examined. In addition, the transducers 8 are positioned at an offset to each other along the flow direction, so that one pulse direction points downstream and the other pulse direction points upstream. For example, the angle of the main beam direction and the main flow direction is in the range of 0° to 85°, advantageously for example in the range of 45° (compromise between placement on the outer wall with a still high parallel portion of the main beam direction to the flow direction).

However, for inter-individual differences of the aortic cross-section 9 and a uniform cuff size, the transducers 8 can—if the cuff 5 is too small and the aortic cross-sectional area 9 is too large—migrate toward 12 o'clock, for example the ultrasonic element 8 shown on the left in FIG. 5 to 10 o'clock and the ultrasonic element 8 shown on the right in FIG. 5 to 2 o'clock. In particular, the ultrasonic measurement discussed above can also be carried out in this case by means of low-focused elements 8 with approximately spherical characteristics. In this case, however, a time of flight based cross-sectional area calculation could possibly have a corresponding error. Because the aortic cross-section 9 is generally on average not subject to major changes versus time, a (known) aortic cross-section, for example predetermined sonographically, can be stored in a calibration data memory (e.g. formed in the control unit 20 of the arrangement 14) as an alternative to the measurement using mean pulse time of flight.

As an alternative to a uniform cuff size, a plurality of devices that differ in the diameter of their retaining means can be specified, for example. During an implantation of the device, the device can then be selected with the appropriate retaining means diameter for the blood vessel.

Furthermore, it can be specified that the sensor 4 can change a main beam direction of the sensor 4. In this context, the measuring accuracy of the system can be further increased in the presence of a swirl or vortex in the blood flow by integrating one or more ultrasonic array transducers instead of single ultrasonic transducers. The measurement plane of the transducers can be pivoted by so-called beam steering, thus advantageously permitting a reconstruction of the complete three-dimensional flow vector field. The method can be generalized to a wave-based interaction means, i.e.—apart from the longitudinal waves present in ultrasound—the effect also occurs in the electromagnetic spectrum in transversal waves, for example of a radar sensor or a laser Doppler velocimeter. In addition to ultrasonic transducers, the integration of radar or laser Doppler sensors is therefore also advantageous, as these can (each) change their main beam direction.

FIG. 6 schematically shows a sequence of a method presented herein in a standard operating procedure.

The method serves to determine a fluid volume flow through a blood vessel in the region of an implanted device. The illustrated sequence of the method steps a), b), and c) with the blocks 110, 120, and 130 results in a standard operating procedure. In block 110, a measurement is carried out with at least one sensor of the device, which is retained with a retaining means for retaining a vessel wall port in the region of a vessel wall of the blood vessel. A measurement result from step a) is provided in block 120. In block 130, the fluid volume flow is determined using the measurement result provided in step b).

The solution presented herein advantageously specifies a device, an arrangement, a method, and a use for determining the total cardiac output (HTV) of a patient with implanted left ventricular cardiac assist system (LVAD). The heart-time volume is an important parameter for assisting the human cardiovascular system with an assist system and can be (continuously) provided in a particularly advantageous manner with the solution proposed herein even outside of cardiac surgery and the subsequent intensive care medical treatment or during routine daily or continuous operation of the implanted assist system. In particular, this parameter (HTV) can be provided continuously as a control parameter for operating the assist system.

The solution proposed herein is based in particular on an integration of, for example, ultrasonic flow metrology into a retaining means for a vessel wall port, for example an aortic wall port as a feed-through for the connecting cable of a ventricular assist system. In particular when the device is located in the region of the aorta, both the blood flow generated by the assist system and the residual output capacity of the heart through the aortic valve past the assist system can thus be advantageously determined.

The solution presented herein in particular has one or more of the following advantages:

• • For fully implanted assist systems, the thorax is opened to position an electronic control component. Access for attaching, for example, a silicone cuff around the aorta is therefore already provided.
  • For (fully) implanted assist systems in the aortic valve position, the supply cable must be guided out of the aorta. The port required for this purpose is suitable as a cuff component for integrating flow metrology, so that no further components need to be integrated.
  • Compared to devices without sensors, only the connection of the additional sensor cable is required during the implantation procedure.
  • The solution allows continuous recording of the cardiac output in patients with a cardiac assist system.

Claims

1.-15. (canceled)

16. A device for determining a blood volume flow through a blood vessel, comprising:

at least one sensor configured to detect at least one flow parameter of blood in the blood vessel, the blood vessel being in fluid communication with a pump of a cardiac assist system,

a retaining means configured to retain a vessel wall port in or on a vessel wall of the blood vessel and configured to retain the at least one sensor in or on the vessel wall.

17. The device according to claim 16, wherein the at least one sensor comprises an ultrasonic element.

18. The device according to claim 16, wherein the at least one sensor is configured to perform a pulsed Doppler measurement.

19. The device according to claim 16, wherein the at least one sensor is configured to record a blood vessel cross-section of the blood vessel.

20. The device according to claim 16, wherein the at least one sensor comprises two ultrasonic elements.

21. The device according to claim 20, wherein the two ultrasonic elements are offset relative to one another in a flow direction of the blood in the blood vessel.

22. The device according to claim 20, wherein the two ultrasonic elements are arranged opposite each other and aligned facing each other.

23. The device according to claim 16, wherein the sensor is configured to change a main beam direction of the sensor.

24. The device according to claim 16, wherein the retaining means comprises a cuff that at least partially circumferentially enwraps the blood vessel.

25. The device according to claim 16, wherein the vessel wall port is configured to receive a portion of the cardiac assist system.

26. The device according to claim 25, wherein the retaining means is configured to position the vessel wall port to receive the portion of the cardiac assist system.

27. The device according to claim 16, wherein the vessel wall port comprises a lead-through for a cable of the cardiac assist system.

28. The device according to claim 16, wherein the vessel wall port comprises an opening for a bypass line of the cardiac assist system.

29. A system comprising:

a cardiac assist system configured to be implanted within a blood vessel; and

a device configured to determine blood volume flow of blood within the blood vessel, the device comprising: at least one sensor configured to detect at least one flow parameter of the blood in the blood vessel; and a retaining means configured to retain a vessel wall port in or on a vessel wall of the blood vessel and configured to retain the at least one sensor in or on vessel wall.

30. The system according to claim 29, wherein the vessel wall port is configured to receive a portion of the cardiac assist system, and wherein the retaining means is configured to position the vessel wall port to receive the portion of the cardiac assist system.

31. The system according to claim 29, wherein the vessel wall port comprises a lead-through for a cable of the cardiac assist system.

32. The system according to claim 29, wherein the vessel wall port comprises an opening for a bypass line of the cardiac assist system.

33. A method for determining a blood volume flow through a blood vessel having a cardiac assist system implanted therein, the method comprising:

performing a measurement with at least one sensor of a device, the device comprising a retaining means configured to retain a vessel wall port in or on a vessel wall of the blood vessel and configured to retain the at least one sensor in or on the vessel wall; and

determining the blood volume flow based at least in part on the measurement.

34. The method according to claim 33, wherein the vessel wall port comprises a lead-through for a cable of the cardiac assist system.

35. The method according to claim 33, wherein the vessel wall port comprises an opening for a bypass line of the cardiac assist system.